WO2011058506A1 - Protection contre la surtension d'un défibrillateur - Google Patents

Protection contre la surtension d'un défibrillateur Download PDF

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Publication number
WO2011058506A1
WO2011058506A1 PCT/IB2010/055109 IB2010055109W WO2011058506A1 WO 2011058506 A1 WO2011058506 A1 WO 2011058506A1 IB 2010055109 W IB2010055109 W IB 2010055109W WO 2011058506 A1 WO2011058506 A1 WO 2011058506A1
Authority
WO
WIPO (PCT)
Prior art keywords
gas discharge
discharge tube
light source
defibrillation
overvoltage protection
Prior art date
Application number
PCT/IB2010/055109
Other languages
English (en)
Inventor
Bruce Andrew Wahler
David K. Hunt
Aziz L'bahy
Original Assignee
Koninklijke Philips Electronics N.V.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Koninklijke Philips Electronics N.V. filed Critical Koninklijke Philips Electronics N.V.
Priority to JP2012538456A priority Critical patent/JP6112864B2/ja
Priority to CN201080051416.6A priority patent/CN102596312B/zh
Priority to BR112012011196A priority patent/BR112012011196A8/pt
Priority to US13/509,450 priority patent/US9901275B2/en
Priority to RU2012125023/14A priority patent/RU2567462C2/ru
Priority to EP10800995.2A priority patent/EP2501436B1/fr
Publication of WO2011058506A1 publication Critical patent/WO2011058506A1/fr

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/276—Protection against electrode failure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/38—Applying electric currents by contact electrodes alternating or intermittent currents for producing shock effects
    • A61N1/39—Heart defibrillators
    • A61N1/3925—Monitoring; Protecting
    • A61N1/3931—Protecting, e.g. back-up systems
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
    • A61B5/28—Bioelectric electrodes therefor specially adapted for particular uses for electrocardiography [ECG]
    • A61B5/283—Invasive
    • A61B5/29—Invasive for permanent or long-term implantation
    • H—ELECTRICITY
    • H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02H—EMERGENCY PROTECTIVE CIRCUIT ARRANGEMENTS
    • H02H9/00—Emergency protective circuit arrangements for limiting excess current or voltage without disconnection
    • H02H9/04—Emergency protective circuit arrangements for limiting excess current or voltage without disconnection responsive to excess voltage
    • H02H9/045—Emergency protective circuit arrangements for limiting excess current or voltage without disconnection responsive to excess voltage adapted to a particular application and not provided for elsewhere

Definitions

  • the field of the present invention relates to a defibrillation circuit, and in particular to overvoltage protection within the defibrillation circuit.
  • the field of the present invention also relates to an overvoltage protection device for medical devices.
  • Defibrillators deliver a high- voltage pulse to the heart in order to restore normal rhythm and contractile function in patients who are experiencing arrhythmia, such as ventricular fibrillation ("VF") or ventricular tachycardia (“VT”) that is not accompanied by a palpable pulse.
  • arrhythmia such as ventricular fibrillation ("VF") or ventricular tachycardia ("VT") that is not accompanied by a palpable pulse.
  • VF ventricular fibrillation
  • VT ventricular tachycardia
  • AEDs automatic external defibrillators
  • AEDs differ from manual defibrillators in that AEDs are pre-programmed to automatically analyze an electrocardiogram (ECG) rhythm to determine if defibrillation is necessary and to provide administration measures such as shock sequences and cardio pulmonary resuscitation (CPR) periods.
  • ECG electrocardiogram
  • CPR cardio pulmonary resuscitation
  • AEDs but possibly also other types of defibrillator, comprise an ECG monitoring circuitry.
  • Some types of defibrillators use the ECG monitoring circuitry to provide a 'demand pacing' function, wherein the ECG monitoring circuitry continually compares the patient's heartbeat to a desired outcome, and provides additional stimulus if the heart cannot maintain its required performance.
  • ECG signals are relatively weak electrical signals.
  • the ECG monitoring circuitry needs to be sensitive enough to detect and analyze the ECG signals.
  • defibrillator also comprises high- voltage circuitry for generating a high- voltage pulse to be administered to the patient.
  • the high-voltage pulse is conducted via a set of defibrillation leads to a set of defibrillation pads which are attached to the patient.
  • the high- voltage circuitry and the ECG monitoring circuitry share the same pads and leads, or the ECG monitoring circuitry is connected to the patient via dedicated monitoring leads and monitoring pads.
  • the high- voltage pulse When a high- voltage pulse is administered to the patient by means of the high- voltage circuitry, the high- voltage pulse is also transmitted to the ECG monitoring circuitry.
  • the ECG monitoring circuitry receives substantially the full high- voltage pulse if the ECG monitoring circuitry shares the defibrillation pads and/or defibrillation leads with the high- voltage circuitry. Even if the ECG monitoring circuitry uses separate monitoring pads and monitoring leads, a significant portion of the high- voltage pulse may reach the ECG monitoring circuitry due to electrical coupling through the body of the patient. Therefore, it is usually necessary to protect the ECG monitoring circuitry in a defibrillator.
  • GDTs Gas discharge tubes
  • spark gap devices are a notable exception: they combine the attributes of moderate clamping voltages, very high impedance in their uncharged state, and fast operation. For these reasons, GDTs are the protection device of choice in ECG monitoring circuitry for modern defibrillators.
  • gas discharge tubes may exhibit an unpredictable behavior with respect to their breakdown voltage and the time it takes for them to change between a high- impedance mode to a short-circuit mode.
  • GDTs require a certain level of steady-state gas ionization activity. Without this ionization, the GDT may remain in its linear operating mode during a high- voltage pulse. The GDT may even remain in the off state for a portion of the high-voltage pulse. While in its linear operating mode the GDT only conducts a relatively small current.
  • the GDT may also take a comparatively long time (several milliseconds) to change state when first excited, risking damage to the circuit that the GDT protects.
  • a traditional method of promoting a prompt arc-over is to add a small amount of radioactive material to the ionizing gas in the GDT. This method is no longer desirable due to environmental and health reasons.
  • defibrillation circuit comprising a gas discharge tube and a light source arranged to pre- energize the gas discharge tube in order to provide predictable breakdown conditions of the gas discharge tube.
  • the light source may pre-energize the gas discharge tube either by ionizing the gas or by means of a photoelectric effect on the anode and/or cathode of the gas discharge tube, which ionizes the gas indirectly.
  • the amount of light output from the light source can be calculated or estimated in advance so that the amount of ionized gas can be estimated, as well. It is thus impossible to determine a range for the breakdown conditions of the gas discharge tube, based on the irradiation conditions provided by the light source.
  • the light source for pre-energizing the gas discharge tube makes the breakdown conditions substantially independent from environmental influences, such as ambient light or temperature. Regardless of whether the gas discharge tube is exposed to ambient light or not, the light source ensures minimal breakdown conditions at which the gas discharge tube will arc over in any event.
  • the light output produced by the light source is used in an efficient manner to pre-energize the gas discharge tube.
  • This desire and/or possible other desires are addressed by the light source being situated in proximity to the gas discharge tube.
  • the light source may also be oriented so that a direction of a maximum light density in a directional characteristic of the light source points to the gas discharge tube.
  • the gas discharge tube would be ready to arc over, i.e. changed from the high- impedance state to the short-circuit state, quickly at any time when a high- voltage pulse may occur.
  • the light source being substantially permanently lit during an operation of the
  • the defibrillation circuit or parts of the defibrillation circuit could be reliably protected against overvoltage.
  • This desire and/or possible other desires are addressed by the gas discharge tube being arranged to function as an overvoltage protection device.
  • the light source It would also be desirable for the light source to be energy-efficient, durable, and/or to produce minimal waste heat. At least one of these desires and/or possible other desires are addressed by the light source being in a form of a light emitting diode (LED). It would be further desirable to protect voltage sensitive components of the defibrillation circuit. This desire and/or possible other desires are addressed by the defibrillation circuit further comprising an electrocardiogram monitoring circuit. The gas discharge tube is connected to the electrocardiogram monitoring circuit to function as an overvoltage protection device for the electrocardiogram monitoring circuit.
  • electrocardiogram monitoring circuit in the defibrillation circuit is usually voltage-sensitive due to the specifications that it has to meet, especially its ability to detect relatively weak voltages and currents.
  • the electrocardiogram monitoring circuit may comprise a plurality of monitoring leads, the defibrillation circuit may comprise an electrical conductor carrying an electrical reference potential sufficient to absorb excess electrical charge and the gas discharge tube may be connected between one of the monitoring leads and the electrical conductor carrying the electrical reference potential.
  • the gas discharge tube arcs over and thus substantially creates a short circuit between the monitoring lead and the electrical conductor. Excess electrical charge present in the monitoring lead is conducted via the gas discharge tube to the electrical conductor carrying the electrical reference potential. The overvoltage between the monitoring lead and the reference potential vanishes or is reduced to a harmless value.
  • the defibrillation circuit may further comprise a plurality of further gas discharge tubes connected between one of the further monitoring leads and the electrical conductor carrying the electrical reference potential.
  • further monitoring leads or all monitoring leads are protected by an individual gas discharge tube.
  • a high-voltage pulse may occur between two of the plurality of monitoring leads so that both gas discharge tubes might arc over in order to connect the two monitoring leads with each other via the electrical conductor carrying the electrical reference potential in a near-short-circuit manner.
  • the defibrillation circuit may further comprise a light-proof or an opaque housing for the gas discharge tube and the light source for providing predictable pre- energizing conditions for the gas discharge tube.
  • the light-proof housing may be the housing of the defibrillation circuit itself, for example the housing of an AED.
  • an overvoltage protection device for a medical device comprising a gas discharge tube and a light source arranged to pre-energize the gas discharged tube in order to provide predictable breakdown conditions of the gas discharge tube.
  • the light source for pre-energizing the gas discharge tube makes the breakdown conditions substantially independent from environmental influences, such as ambient light or temperature. Regardless of whether the gas discharge tube is exposed to ambient light or not, the light source ensures minimal breakdown conditions at which the gas discharge tube will arc over in any event.
  • the light source may be situated in proximity to the gas discharge tube.
  • the light source may be substantially permanently lit during the armed state (operational state) of the overvoltage protection device.
  • the light source may be a light emitting diode (LED).
  • LED light emitting diode
  • Fig. 1 shows a schematic block diagram of a first embodiment of a defibrillation circuit according to the teachings disclosed herein.
  • Fig. 2 shows a schematic block diagram of another embodiment of the defibrillation circuit according to the teachings disclosed herein.
  • Fig. 3 shows a chart illustrating the effect of the teachings disclosed herein.
  • FIG. 1 shows in a schematic manner a block diagram of a defibrillation circuit according to the teachings disclosed herein.
  • the defibrillation circuit comprises a high- voltage circuit 102 arranged to deliver a high- voltage pulse to a patient requiring defibrillation.
  • the high-voltage circuit 102 is connected to defibrillation pads 106, 108 by means of two defibrillation leads 105, 107.
  • the defibrillation pads 106, 108 may be adhesive pads that are attached to the patient prior to the beginning of a defibrillation procedure.
  • the defibrillation circuit further comprises an electrocardiogram (ECG) monitoring circuit 104.
  • ECG monitoring circuit 104 is indirectly connected to the defibrillation pads 106, 108 by means of two monitoring leads 115, 117, which are connected to the defibrillation leads 105 and 107 respectively.
  • ECG monitoring circuit 104 is indirectly connected to the defibrillation pads 106, 108 by means of two monitoring leads 115, 117, which are connected to the defibrillation leads 105 and 107 respectively.
  • only two electrode pads are needed because the defibrillation pads 106, 108 are also used for ECG monitoring.
  • Having only two defibrillation pads 106, 108 facilitates a quick placement of the defibrillation pads 106, 108 especially in case the defibrillator is used by a lay person.
  • the ECG monitoring circuit 104 receives the high- voltage pulse (or a significant part thereof) because of the direct galvanic connection between the high- voltage circuit 102 and the ECG monitoring circuit 104. While the ECG monitoring circuit 104 may be designed to withstand normal high- voltage pulses by the high- voltage circuit 102, it is possible that the ECG monitoring circuit 104 receives overvoltage pulses. For example, one of the defibrillation pads 106, 108 might not be properly attached to the patient so that no current or only a small current can flow via the interface between the defibrillation pad and the skin of the patient.
  • the high- voltage pulse tends to be discharged via another conducting path than the patient.
  • This other conducting path may comprise the ECG monitoring circuit 104.
  • the ECG monitoring circuit 104 comprises terminals that are used for connecting the monitoring leads 115, 117 with the ECG monitoring circuit 104.
  • the terminals of the ECG monitoring circuit are also connected to overvoltage protection devices, respectively.
  • a first overvoltage protection device comprises a gas discharge tube 125 which is connected to the ECG monitoring lead 115 at a first terminal of the gas discharge tube 125.
  • the gas discharge tube 125 is also connected to an electrical ground potential 130 at another terminal of the gas discharge tube 125.
  • a light emitting diode (LED) 135 is located in a proximity to the gas discharge tube 125.
  • a resistor 136 is connected in series with the light emitting diode 135 and also to a 5 volt electrical potential (5V).
  • the light emitting diode 135 is also connected to the electrical reference potential 130.
  • the series resistor 136 limits a current flowing through the light emitting diode 135 to a value that is suited for a long-term operation of the light emitting diode 135 and yields a sufficient light output of the LED 135.
  • the light output produced by the light emitting diode 135 is directed in the direction of the gas discharge tube 125.
  • the gas discharge tube 125 becomes pre-energized due to an ionizing effect of the light from the LED 135 on the gas contained in the gas discharge tube 125.
  • Another effect that may become relevant is the photoelectric effect by which electrons may be liberated in the anode or the cathode of the gas discharge tube 125.
  • the ECG monitoring lead 117 is also connected to a gas discharge tube 127 which is, in turn, connected to the electrical reference potential 130.
  • a light emitting diode 137 LED
  • a series resistor 138 limits a current flowing through the light emitting diode 137.
  • the series resistor 138 is also connected to a 5 volt electrical potential 5V, which could be the same as described previously in connection with the light emitting diode 135 and the series resistor 136.
  • 5V another electrical potential adapted to operate a light emitting diode could be used, such as 3V.
  • the emitting diode 135, 137 could also be connected to some control circuitry in order to switch the light emitting diode 135, 137 on and off as required. It is also possible to use a variable resistor in addition to the series resistors 136 or 138, or as a replacement for the resistor 136 or 138. The variable resistor could be used to change the current flowing through the light emitting diode 135 or 137, thus adjusting the light output of the light emitting diode. In turn, the break down conditions of the gas discharge tube 125 or 127 could be adjusted within a certain range.
  • Figure 2 shows in a schematic manner a block diagram of a defibrillation circuit according to another embodiment of the teachings disclosed herein.
  • the high- voltage part is basically unchanged compared to Figure 1.
  • the high- voltage part comprises the high-voltage circuit 102, the defibrillation leads 105, 107 and the defibrillation pads 106, 108.
  • the ECG monitoring part of the defibrillation circuit shown in Figure 2 is separate from the high- voltage part.
  • the ECG monitoring pads comprises three ECG monitoring pads 214, 216, 218 (could be only two ECG monitoring pads or more than three ECG monitoring pads).
  • the first ECG monitoring pad 214 is connected to an ECG monitoring lead 213 for connection to the ECG monitoring circuit 204.
  • the second ECG monitoring pad 216 is connected to a second ECG monitoring lead 215 for connecting to the ECG monitoring circuit 204 and the third ECG monitoring pad 218 is connected to a third ECG monitoring lead 217 for connection to the ECG monitoring circuit 204.
  • a coupling 210 occurs between the defibrillation pads 106, 108 and the ECG monitoring pads 214, 216, 218.
  • the ECG monitoring leads 213, 215, 217 are overvoltage protected by means of individual gas discharge tubes 223, 225, 227, connected to the reference potential 130.
  • pre-energizing the gas discharge tubes 223, 225, 227 is achieved by light emitting diodes 233, 235, 237.
  • the supply circuitry for the various light emitting diodes 233, 235, 237 is not illustrated in Figure 2.
  • the gas discharge tube 223, 225, 227 in Figure 2 may be chosen to have a lower break down voltage and thus to more efficiently protect the ECG monitoring circuit 204.
  • the reason is that there is no direct galvanic coupling between the high- voltage part and the ECG monitoring part of the defibrillation circuit. Shorting the ECG monitoring leads 213, 215, 217 to the reference potential 130 in response to a high- voltage pulse administered by the high- voltage circuit 102 does not have a large influence on the high- voltage pulse experienced by the patient.
  • Figure 3 shows a schematic diagram of an effect of pre-energizing the gas discharge tube 127 with light.
  • the break down voltage V BREAKDOWN is relatively high and may assume any value within a relatively large range of possible breakdown voltages. This is especially true for a first arcing-over event of the gas discharge tube 127 after some time of inactivity. The reason is that only a few gas molecules inside the gas discharge tube 127 are energized for the purposes of overvoltage protection. Without adequate pre-energization it cannot be relied upon the gas discharge tube arcing over at a certain desired voltage.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Public Health (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Veterinary Medicine (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Cardiology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Physics & Mathematics (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Electrotherapy Devices (AREA)
  • Radiation-Therapy Devices (AREA)

Abstract

Le circuit de défibrillation ci-décrit comprend un tube à décharge de gaz et une source lumineuse conçue pour pré-exciter le tube à décharge de gaz afin de créer les conditions de rupture prévisibles du tube à décharge de gaz. Le tube à décharge de gaz peut être utilisé comme un dispositif de protection contre la surtension du circuit de défibrillation ou de certaines parties dudit circuit de défibrillation. Un dispositif de protection contre la surtension de dispositifs médicaux est également décrit. Ce dispositif de protection contre la surtension comprend un tube à décharge de gaz et une source lumineuse conçue pour pré-exciter le tube à décharge de gaz afin de créer les conditions de rupture prévisibles du tube à décharge de gaz.
PCT/IB2010/055109 2009-11-16 2010-11-10 Protection contre la surtension d'un défibrillateur WO2011058506A1 (fr)

Priority Applications (6)

Application Number Priority Date Filing Date Title
JP2012538456A JP6112864B2 (ja) 2009-11-16 2010-11-10 除細動器に関する過電圧保護
CN201080051416.6A CN102596312B (zh) 2009-11-16 2010-11-10 用于除颤器的过压保护
BR112012011196A BR112012011196A8 (pt) 2009-11-16 2010-11-10 Circuito de desfibrilação, dispositivo de proteção contra sobretensão para dispositivos médicos e método para utilizar um tubo de liberação de gás em um dispositivo médico
US13/509,450 US9901275B2 (en) 2009-11-16 2010-11-10 Overvoltage protection for defibrillator
RU2012125023/14A RU2567462C2 (ru) 2009-11-16 2010-11-10 Защита от перенапряжения для дефибриллятора
EP10800995.2A EP2501436B1 (fr) 2009-11-16 2010-11-10 Protection contre la surtension d'un défibrillateur

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US26138909P 2009-11-16 2009-11-16
US61/261,389 2009-11-16

Publications (1)

Publication Number Publication Date
WO2011058506A1 true WO2011058506A1 (fr) 2011-05-19

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ID=43530356

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/IB2010/055109 WO2011058506A1 (fr) 2009-11-16 2010-11-10 Protection contre la surtension d'un défibrillateur

Country Status (7)

Country Link
US (1) US9901275B2 (fr)
EP (1) EP2501436B1 (fr)
JP (1) JP6112864B2 (fr)
CN (1) CN102596312B (fr)
BR (1) BR112012011196A8 (fr)
RU (1) RU2567462C2 (fr)
WO (1) WO2011058506A1 (fr)

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Publication number Priority date Publication date Assignee Title
US9872619B2 (en) * 2015-01-05 2018-01-23 Salutron Inc. Physiological sensor pod with reset circuit
RU2649825C1 (ru) * 2016-06-22 2018-04-04 Общество с ограниченной ответственностью "Кардиотехника" Устройство для передачи биофизиологических сигналов
CN108785049B (zh) * 2018-04-17 2020-06-09 广东工业大学 一种胸外按压频率的测量装置
CN108939296A (zh) * 2018-06-06 2018-12-07 广东紫薇星实业有限公司 一种用于保护磁疗装置供电电路过压的方法
CN109149510A (zh) * 2018-10-26 2019-01-04 北京柔云科技有限责任公司 心电贴片的电子电路全路径保护装置

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US20060155354A1 (en) * 2005-01-13 2006-07-13 Heath Roger L Electrode system for a physiological stimulator
US20090210022A1 (en) 2006-05-16 2009-08-20 Koninklijke Philips Electronics, N.V. Simplified biphasic defibrillator circuit with make-only switching

Also Published As

Publication number Publication date
CN102596312A (zh) 2012-07-18
JP2013510631A (ja) 2013-03-28
CN102596312B (zh) 2015-09-23
JP6112864B2 (ja) 2017-04-12
EP2501436B1 (fr) 2016-08-24
US9901275B2 (en) 2018-02-27
RU2012125023A (ru) 2013-12-27
BR112012011196A2 (pt) 2017-09-19
BR112012011196A8 (pt) 2017-10-10
EP2501436A1 (fr) 2012-09-26
US20130131526A1 (en) 2013-05-23
RU2567462C2 (ru) 2015-11-10

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